DOI: http://dx.doi.org/10.1590/1980-5373-MR-2017-0659Materials Research. 2018; 21(3): e20170659

Effect of Temperature, Electrolyte Composition and Immersion Time on the Electrochemical Corrosion Behavior of CoCrMo Implant Alloy Exposed to Physiological Serum and Hank's

Solution

Jéferson Aparecido Moretoa*, Adriana Costa Rodriguesa, Rafaela Rodrigues da Silva Leiteb,

Alexandre Rossia, Luís Antônio da Silvaa, Valéria Almeida Alvesa

Received: July 17, 2017; Revised: November 12, 2017; Accepted: February 28, 2018

A new study about corrosion behavior of CoCrMo alloy used as implant material exposed to the physiological serum and Hank's solution in different temperatures, electrolyte compositions and immersion time were simulated, using open circuit potential (OCP), potentiodynamic polarization curves (PPC) and electrochemical impedance spectroscopy (EIS.) From the results, it can be concluded that CoCrMo biomaterial is influenced by electrolyte composition and temperature, and the passive films were more protective when formed in presence of physiological serum. Comparing the Ecorr for both solutions, it is possible to verify that the Hank's solution presented values more negative for the two studied temperatures (25 and 37 °C), indicating a greater susceptibility to the corrosion process. Regarding the results of potentiodynamic polarization, the ipass, decreased as function of time, indicating a more protective passive film at 25 °C. In regards to the physiological serum, the highest ipass values at 37 ºC evidenced the formation of a less stable passive film. The different behavior of ipass in Hank's solution may be related to the competitiveness between a possible film of D-glucose and oxides of the alloy metals. EIS studies suggest that the film formed in presence of physiological serum is nobler than that with Hank's solution.

Keywords: Passivation current, Global electrochemical techniques, Biomedical application, Corrosion resistance.

*e-mail: jeferson.moreto.uftm@gmail.com

1. Introduction

Implant materials are usually metallic materials like titanium alloys, Co-based alloys and austenite stainless steels1. The Cobalt-Chromium-Molybdenum (CoCrMo) based alloys are widely used for orthopedic implants and dental skeletal structures, such as screws, pins and plates2-4. The CoCrMo alloys are also found in industrial applications, such as wind turbines, engine components and bearings. The advantages of using these alloys are due to their better bulk mechanical properties, in particular their wear resistance and strength combined with corrosion resistance and biocompatibility. The CoCrMo alloys spontaneously form on their surfaces a passive, protective film, mostly Cr2O3.

Buciumeanu et al.5 studied the tribocorrosion behavior of hot pressed CoCrMo alloys in artificial saliva. According to the authors, the degradation of biomaterials is a complex phenomenon, because it operates in a corrosive environment. In fact, the corrosion resistance of a biomaterial is determined

by the characteristics of this passive film6. Thus, the study of the corrosion resistance of metallic biomaterials is essential, since this is one of the key factors that determines their biocompatibility. The release of the toxic metallic ions can lead to various adverse tissue reactions and/or hypersensitivity reactions7. The uniform passive dissolution resulted from the slow diffusion of metal ions through the passive film, and the local breakdown of the passivity as a consequence of the various types of localized corrosion, or various mechanical events, such as fretting corrosion8-11.

Despite their applications in orthopedics, which are mainly based on their corrosion resistance, the electrochemical properties of CoCrMo alloys have not been extensively investigated until now, having been considered scarce in literature6,12-22. According to Bettini et al.23, many works have been focused on the influence of the microstructure on the wear and mechanical properties of CoCrMo alloy. However, little is known about its influence on the corrosion behavior of CoCrMo alloy.

aInstituto de Ciências Exatas, Naturais e Educação, Universidade Federal do Triangulo Mineiro (UFTM), Avenida Doutor Randolfo Borges Júnior, Univerdecidade, 38.064-200, Uberaba, MG, Brasil

bDepartamento de Farmácia, Universidade Federal dos Vales do Jequitinhonha e Mucuri, Rodovia MGT 367 - Km 583, 5000, 39100-000, Diamantina, MG, Brasil

Moreto et al.2 Materials Research

Although the quantity of information concerning the electrochemical corrosion resistance and chemical properties of the passive film formed on the CoCrMo biomaterial seems sufficient, there is a certain difficulty in comparing the results from different authors, since the parameters in which the experiments were conducted vary, such as with temperature, electrolyte composition, time of immersion and potential in which the electrochemical measurements were done. The present research was aimed at characterizing CoCrMo alloy by electrochemical methods, to understand the effect of the electrolyte composition, temperature and immersion time on the corrosion resistance of this material. The electrochemical studies were carried out in presence of Hank's and physiological serum solutions (0.9 wt% NaCl) at two temperatures (25 and 37 oC.) The Electrochemical properties of the CoCrMo alloy were characterized using open circuit potential (OCP) measurements, potentiodynamic polarization curves (PPC) and electrochemical impedance spectroscopy (EIS).

2. Materials and Methods

2.1. Chemical composition

For the present investigations, the CoCrMo alloy (donated by MDT Ltda) was used in the following conditions. Table 1 lists the chemical composition of the major elements.

2.2. Electrochemical measurements

2.2.1. Open circuit potential and potentiodynamic polarization

Standard electrochemical corrosion procedures were followed. The tests began with an open circuit potential (OCP), in which the corrosion potential (Ecorr) of the samples was monitored during 7 h, in the presence of physiological serum and Hank's solution. Potentiodynamic polarization followed the ASTM G61 standard, and the measurements were made in the range -50 mV, to show the potential in which the anodic current was 500 µA, with a potential sweep rate of 2.5 mV s-1, using a potentiostat/galvanostat from AUTOLAB® (Eco Chemie, The Netherlands), model PGSTAT10, and the software GPES® (General Purpose Electrochemical System.) The measurements were taken at specific immersion times of 5 min and 168 h, using an aerated physiological serum (0.9 wt% NaCl) and Hank's solution (pH 7.5.) To summarize, the samples were mechanically polished using abrasive papers from 320# to 4000# prior

to electrochemical corrosion testing. After, the samples were degreased with propanol and cleaned carefully with distilled water.

2.2.2. Electrochemical impedance spectroscopy tests

Electrochemical impedance spectra (EIS) were obtained for CoCrMo alloy using the same solution as described before, in the frequency range of 65 kHz to 10 mHz, using a sinusoidal perturbation of 10 mV (rms.) All the above electrochemical experiments were conducted using a classical three-electrode configuration: the CoCrMo alloy as working electrode with an exposed area of 0.785 cm2, a Ag/AgCl/KCl, AgCl (sat.) as reference electrode and a platinum auxiliary electrode. A thermostatic bath from Tecnal®, model TE-2005, was used to maintain the desired temperature. The reference electrode was kept at ~4 mm from the sample, in order to minimize the ohmic drop. For EIS data fitting, the Equivcrt® software was used24-25. To ensure linearity of the electrode response, a small amplitude sine wave (5 mV (p/p)) was used throughout the experiment.

3. Results and Discussion

3.1. Open circuit potential (OCP) and Potentiodynamic Polarization Curves (PPC)

The OCP measurements were carried out on the CoCrMo alloy as a function of immersion time, in the presence of physiological serum (0.9 wt% NaCl) and Hank's solution (pH 7.5), at temperatures of 25 and 37 °C, as shown in Figure 1.

Comparing the corrosion potential (Ecorr) for both solutions, it is possible to verify that the Hank's solution presented values more negative for the two temperatures studied, indicating a greater susceptibility to the corrosion process as described by Moreto et al.26. It is important to note that in the presence of the physiological serum solution at 37 oC, the CoCrMo alloy presented transient currents, indicating a competition between the anodic and cathodic regions. The difference in composition between the depleted chromium and the matrix compositions leads to a difference in the corrosion potentials that affected the dissolution of the CoCrMo alloy27.

Figures 2 and 3 show the PPC curves of CoCrMo alloy, in the presence of physiological serum and Hank's solutions, respectively.

The PPC curves (Figures 2 and 3) for CoCrMo alloy were performed after 5 min and 168 h of immersion, at 25

Table 1. Chemical composition (wt%) of the CoCrMo alloy

Cr Mo Si Mn Fe Ni C N W Al Ti

27.00-30.00 5.00-7.00 1.00 1.00 0.75 0.50 0.35 0.25 0.20 0.10 0.10

Co: balance

3Effect of Temperature, Electrolyte Composition and Immersion Time on the Electrochemical Corrosion Behav-ior of CoCrMo Implant Alloy Exposed to Physiological Serum and Hank's Solution

Figure 1. Influence of temperature on open circuit potential measurements, as a function of time for physiological serum and Hank's solution.

Figure 2. Potentiodynamic polarization curves of CoCrMo in physiological serum, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC.

Figure 3. Potentiodynamic polarization curves of CoCrMo in Hank's solution, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC.

Moreto et al.4 Materials Research

and 37 oC, for both solutions. All experiments in this study were repeated at least three times to ensure reproducibility. As was seen in the PPC curves, there was a region of passive film formation that appeared at different immersion times and temperatures.

Table 2 shows the values of Ecorr obtained from the PPC curves. Qualitative analysis of the PPC curves shows that the Ecorr shifts to less negative values when immersion time increases.

The passivation current, ipass, was measured for CoCrMo alloy at specific potentials of +0.2 V (in physiological serum, at 25 and 37 oC) and +0.1 V (in Hank's solution, at 25 and 37 oC) in 5 min and 168 h. These potential values are localized in the passive range of the potentiodynamic polarization. Figures 4 (a) and 4 (b) show ipass as a function of immersion time for CoCrMo alloy, at both temperatures and in presence of physiological serum and Hank's solution, respectively. At 25 oC, the ipass values decrease as function of time, indicating a more protective passive film. In physiological serum, the highest ipass values at 37 ºC evidenced the formation of a less stable passive film. The different behavior of ipass in Hank's solution may be related to the competitiveness between a possible film of D-glucose and oxides of the alloy metals. At 5 min, the D-glucose film better protects the surface at 37 °C, inhibiting metal corrosion. At the time of 168 h, the disruption of the D-glucose film occurs, exposing the metal surface to the dissolution process.

3.2. Electrochemical impedance spectroscopy measurements (EIS)

Impedance spectra for CoCrMo alloy at two different immersion times (5 min and 168 h) and two different temperatures (25 and 37 oC) are presented in Figures 5 to 8, in physiological serum and Hank's solutions, respectively (Nyquist diagram and Bode plots).

The semicircles in the Nyquist diagram find the centers of origin displaced, relative to the real axis, which indicates a situation of "depression," indicating the irregular characteristics of the surface of the CoCrMo alloy. Regarding the Bode diagrams, it is possible to observe two time constants for 168 h of immersion, while for the immersion time of 5 min, the two time constants are superimposed. In both time constants, the irregular surfaces of the CoCrMo alloy cause a phase angle of less than -90°.

The equivalent circuit depicted in Figure 9 was proposed to describe the behavior of this kind of material.

The components of this equivalent circuit are: RΩ, ohmic resistance of the electrolyte, and the loop Qf-Rf, respectively, the capacitance and resistance of the oxide layer and the Qdl-Rct network that represents the charge transfer reactions corresponding to localized corrosion and the capacitance of the double layer. The Impedance spectra were fitted to this circuit, resulting in a very good correlation. Tables 3 and 4 provide the typical values of the fitting results parameters for CoCrMo alloy under different electrolyte compositions, different immersion times and different temperatures.

As is observed, the RΩ remains more or less constant. As reported by Moreto et al.26, the RΩ depends on the distance between the working and the reference electrodes, which was kept constant in this survey, and on the solution concentration, which is not expected to change within the short duration of the immersion tests. However, it is important to note that all resistance values decreased with increasing temperature, regardless of the electrolyte used.

Table 2. Corrosion potential for CoCrMo alloy in the presence of physiological serum and Hank's solution, at 5 min and 168 h at different temperatures

Immersion timeEcorr/ V

Electrolyte composition

Physiological serum Hank's solution

25 ºC

5 min -0.35 -0.46

168 h -0.16 -0.36

37 ºC

5 min -0.39 -0.48

168 h -0.23 -0.24

This confirms that changes occurred on the metallic surfaces, as a result of the formation of a protective passive film, which leaves the surfaces more noble with time, or more corrosion resistant. In the physiological serum solution, the Ecorr shifted to more negative values with increasing temperature (25 and 37 °C) and immersion time (5 min and 168 h), indicating the greater aggressiveness of the medium in the corrosion process. In the Hank's solution, the Ecorr comportment with the temperature was opposite of that observed in the physiological serum solution, with no significant change in 5 min of immersion, and moving to less negative values after one week of immersion. It is probably that the D-glucose reagent from Hank's solution composes the passivating film28-29.

The CoCrMo alloy presents an extensive potential region where the current remained constant with potential for increase, which corresponds to the passive film formation upon potential application. At potentials higher than ~ + 0.6 V were observed with an increase in the current density with the potential, for both solutions and temperatures (see Figures 2 and 3). According to Giacomelli et al.30, the increase of current is due to transpassivation and oxygen evolution reaction. It is important to note that in ~ + 0.65 V, one oxidation peak was observed in the curves from Hank's solution (see, Figure 3). It is likely the oxidation peaks are due to electrochemical reactions involving transitions of chromium to high oxidation states, as described by Giacomelli et al.30. The electrolyte composition shows influence on the electrochemical corrosion behavior of the CoCrMo alloy.

5Effect of Temperature, Electrolyte Composition and Immersion Time on the Electrochemical Corrosion Behav-ior of CoCrMo Implant Alloy Exposed to Physiological Serum and Hank's Solution

Figure 4. Current passivation, ipass, values of CoCrMo, as a function of immersion time, at 25 oC and 37 oC. (a) Physiological serum and (b) Hank's solution.

Figure 5. Nyquist diagram of CoCrMo alloy in physiological serum, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC. The black line represents the fitting obtained by using the electric circuit.

Figure 6. Nyquist diagram of CoCrMo alloy in Hank's solution, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC. The black line represents the fitting obtained by using the electric circuit.

Moreto et al.6 Materials Research

Figure 7. Bode-phase and Bode-magnitude spectra of CoCrMo alloy, in physiological serum, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC. The black line represents the fitting obtained by using the electric circuit.

Figure 8. Bode-phase and Bode-magnitude spectra of CoCrMo alloy, in Hank's solution, as a function of immersion time, at (a) 5 min and (b) 168 h, at 25 oC and 37 oC. The black line represents the fitting obtained by using the electric circuit.

Figure 9. Equivalent circuit used for modeling the CoCrMo/solution: [RΩ(Qf[Rf(QdcRct)])]

Comparing the results for all conditions, Qf values tend to increase with the immersion time. The increase of Qf with the immersion time at the two temperatures represents the better organization and greater stability of the oxide film formed on the surface of the CoCrMo alloy as described by equation (1):

(1)

where ε0 is the vacuum permittivity (8.85 pF/m), A is the sample surface area, d is the thickness and ε is the dielectric constant26. The dielectric constant of chromium oxide and iron oxide is approximately 1231. With regard to aluminum alloys, the dielectric constant is 9 for the dry oxide layer (lower bound) and 40 for a partially hydrated layer (upper bound)32. The dielectric constant of the passive film (~60)33 for titanium dioxide TiO2 and ~25 for tantalum pentoxide (Ta2O5)

34.Analyzing the values of Qf at 25 oC as a function of

immersion time, it is possible to verify that physiological serum solution presents a smaller variation (~17.87%) when comparing to the Hank´s solution. However, the opposite effect was observed at 37 oC. This anomalous behavior may be explained due to D-glucose film formation and subsequent adsorption instability on the surface of the CoCrMo alloy, as already discussed before.

The values of Qdl shows a tendency towards higher values, with the immersion time for the physiological serum and Hank´s solution at 25 and 37 oC. According to equation (2), the increase of Qdl may be associated with the real area where the corrosion process is taking place. The dominant corrosion protection in all CoCrMo alloys is a thin film of

Q dA

f0ff=

7Effect of Temperature, Electrolyte Composition and Immersion Time on the Electrochemical Corrosion Behav-ior of CoCrMo Implant Alloy Exposed to Physiological Serum and Hank's Solution

Figure 10. Charge transference resistant, Rct, values of CoCrMo, as a function of immersion time, at 25 oC and 37 oC. (a) Physiological serum; (b) Hank's solution

Table 3. Fitting parameters obtained from the average of three impedance measurements for CoCrMo alloy, in presence of physiological serum at 5 min and 168h

Temperature RΩ(Ω cm2)

Rf(kΩ cm2)

Qf(µF cm-2) nf

Rct(kΩ cm2)

Qdl(µF cm-2) ndl

Immersion time: 5 min

25 ºC 18.42 1.77 12.81 0.97 30.68 38.96 0.57

37 ºC 15.75 1.74 16.32 0.94 22.90 40.07 0.65

Immersion time: 168 h

25 ºC 18.70 3.50 23.21 0.89 63.26 46.08 0.73

37 ºC 15.18 2.87 28.94 0.85 26.60 95.44 0.68

Table 4. Fitting parameters obtained from the average of three impedance measurements for CoCrMo alloy, in presence of Hank's solution, at 5 min and 168 h

Temperature RΩ(Ω cm2)

Rf(kΩ cm2)

Qf(µF cm-2) nf

Rct(kΩ cm2)

Qdl/(µF cm-2) ndl

Immersion time: 5 min

25 ºC 18.41 5.72 17.65 0.92 85.96 27.96 0.62

37 ºC 14.46 5.16 22.39 0.91 57.68 31.74 0.72

Immersion time: 168 h

25 ºC 17.86 5.93 27.00 0.81 64.80 67.79 0.69

37 ºC 14.48 0.94 16.29 0.73 15.63 76.19 0.60

chromium oxide (Cr2O3). As this alloy corrodes, the mass loss of material is not constant; there is often preferential corrosion28. The analysis of Rct values on the CoCrMo alloy shows a tendency towards lower values as the immersion time increases. These results are in agreement with the increase of Qdl values. As can be seen, the Rct values are always higher for the physiological serum solution at 25 and 37 oC, indicating a better performance than Hank's solution in the same condition of tests, see Figure 10.

For the CoCrMo alloy in presence of the Hank's solution, no clear treads were observed for the Rct values, as described by equation (3), exhibiting that the corroded area (Acorroded) is increasing for both temperatures. This phenomenon probably has a relation with the formation of a porous film and with the adsorption of ions. The variables presented in equations 2 and 3 are: corroded area (Acorroded), geometric area (Ageom), Qdl*- Rct* network that represents the apparent charge transfer reactions corresponding to localized corrosion and the capacitance of the double layer.

Moreto et al.8 Materials Research

(2)

(3)

It was possible to verify that the increase in temperature facilitates the removal of D-glucose on the surface of the CoCrMo alloy. It is believed that the increase in temperature caused a rupture of the formed oxide film and facilitated the charge transfer process. This presents a situation in which, the electrolyte composition is shown to influence the electrochemical corrosion behavior of the CoCrMo alloy. The EIS results suggest that the formed film in presence of physiological serum solution is nobler than Hank's solution.

4. Conclusions

In the present work, we studied the corrosion behavior of CoCrMo alloy and the effect of temperature, electrolyte composition and immersion time, using electrochemical techniques (open circuit potential, potentiodynamic polarization and electrochemical impedance spectroscopy). It is possible to verify that the corrosion behavior of CoCrMo alloy is influenced by electrolyte composition and temperature. It was shown that the passive films were more protective when formed in the presence of physiological serum. The increase in temperature facilitates the removal of D-glucose on the surface of the CoCrMo alloy for the Hank´s solution, creating a rupture of the formed oxide film, and facilitating the charge transfer process. This presents a situation in which, the EIS results show that the formed film, in the presence of physiological serum solution, is nobler than Hank's solution. The Rct values had an inverse behavior when it came to the increase of the immersion time for the solutions of serum and Hank. The decrease of Rct values for Hank's solution is probably due to the formation of a porous film of D-glucose on the surface of the material, allowing greater charge transfer. These results corroborate the ipass values. As regards the physiological serum solution, the values of Rct increased with the immersion, indicating the formation of a more protective film to the corrosion process.

5. Acknowledgments

Financial support from Projects and Studies Financing Institution (FINEP) (process 01.06.0243.00) and Foundation for Research Support of Minas Gerais (FAPEMIG) (processes CDS 12/03 and CEX 1736/06). This work is a collaboration research project of members of the Rede Mineira de Química (RQ-MG), supported by FAPEMIG (project: REDE-113/10 and project: CEX - RED-00010-14) and the National Council for Scientific and Technological Development (CNPq).

Conflict of interest: The authors declare that they have no conflict of interest.

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